Minimally-invasive low strain annuloplasty ring

ABSTRACT

A minimally-invasive annuloplasty ring for implant at a mitral annulus. The annuloplasty ring has an inner core member with a C-shaped plan view that generally defines an oval with a major axis and a minor axis, and is symmetric about the minor axis. A posterior portion of the core member bisected by the minor axis has a thicker radial dimension than a pair of free end regions terminating on an anterior side of the core member. The radial thickness smoothly transitions between the posterior portion and the end regions. The inner core member may be covered with a fabric, and is a superelastic metal so that it can be straightened out and delivered through an access tube. The curvatures and thicknesses around the core member are selected so that the strain experienced when straightened does not exceed 7-8%.

CROSS REFERENCE TO RELATED APPLICATIONS

This application is a continuation of International Application No. PCT/US2019/043864, filed Jul. 29, 2019, which claims the benefit of U.S. Application No. 62/711,949, filed Jul. 30, 2018, the entire contents all of which are incorporated herein by reference for all purposes.

TECHNICAL FIELD

The present invention relates generally to cardiac implants and particularly to minimally-invasive annuloplasty rings that may be implanted at the native mitral or tricuspid heart valve annulus.

BACKGROUND

In vertebrate animals, the heart is a hollow muscular organ having four pumping chambers: the left and right atria and the left and right ventricles, each provided with its own one-way valve. The natural heart valves are identified as the aortic, mitral (or bicuspid), tricuspid and pulmonary, and are each mounted in an annulus comprising dense fibrous rings attached either directly or indirectly to the atrial and ventricular muscle fibers. Each annulus defines a flow orifice.

Prosthetic annuloplasty rings are used to repair or reconstruct damaged or diseased heart valve annuluses. An annuloplasty ring is designed to support the functional changes that occur during the cardiac cycle: maintaining coaptation and valve integrity to prevent reverse flow while permitting good hemodynamics during forward flow. The annuloplasty techniques may be used in conjunction with other repair techniques. The rings either partially (C-shaped) or completely (D-shaped) encircle and are secured to the valve annulus, and may be rigid, flexible, or semi-flexible.

Although mitral and tricuspid valve repair can successfully treat many patients with valve problems, techniques currently in use are attended by significant morbidity and mortality. Most valve repair and replacement procedures require the entire sternum of the patient is divided from top to bottom to gain access to the patient's thoracic cavity as well as the use of cardiopulmonary bypass. There are a number of significant drawbacks to current methods.

Currently, there is a move in cardiovascular surgery toward minimally invasive surgery (MIS), which essentially means performing procedures such as valve replacement and repair through smaller than traditional surgical exposure. MIS procedures generally involve a partial sternotomy, in which only a portion of the sternum is divided, or a thoracotomy, in which an incision is made between ribs. Particularly in the latter case, the surgical exposure is very limited and poses a new set of challenges compared to a full open procedure. Surgeons have become very adept at operating though these small openings, and surgical instruments and support devices exist to facilitate such procedures, but adaptations of annuloplasty rings that can easily be inserted through such small openings are required.

What is needed are devices and methods for annuloplasty rings which could be configured to pass through a small opening or tube while retaining a pre-defined shape and a desired amount of rigidity.

SUMMARY

The present application provides minimally-invasive annuloplasty ring for implant at a mitral annulus. The annuloplasty ring has an inner core member with a C-shaped plan view. A middle or posterior portion of the core member has a thicker radial dimension than a pair of free end regions terminating on an anterior side of the core member. The radial thickness smoothly transitions between the posterior portion and the end regions. The inner core member is a superelastic metal so that it can be straightened out and delivered through an access tube. The curvatures and thicknesses around the core member are selected so that the strain experienced when straightened does not exceed 7-8%.

Compared to current repair rings, the disclosed device is able to be elastically straightened such that it can be delivered through a small surgical opening and/or a tube such as a catheter. The disclosed annuloplasty ring has dimensions which maximize stiffness while allowing the device to be completely straightened out during delivery. More specifically, the ring has matched radii and radial thicknesses around its periphery which in cooperation result in a strain below the yield strain of nitinol when the ring is straightened out for MIS delivery.

One embodiment comprises an annuloplasty ring which is designed specifically such that it can be temporarily flexed from a generally “C” shaped ring into a linear shape for passage through a very small surgical opening and/or a tube or catheter. The disclosed ring takes advantage of the large elastic strains achievable with superelastic materials such as nitinol.

An exemplary embodiment of an annuloplasty ring comprises an inner core member surrounded by an outer covering. The inner core member is formed of a superelastic material and defines a curved relaxed implant shape in plan view which has two free ends spaced across a gap and at least two regions of different curvatures therebetween around a periphery of the core member. The core member has a radial thickness in each region which, in cooperation with a respective curvature in that region, limits a strain within the superelastic material when the ring is substantially straightened to below the yield strain of the superelastic material. Consequently, the annuloplasty ring can be temporarily flexed from its relaxed shape into a linear shape for passage through an access tube or catheter. The superelastic material may be nitinol, and the yield strain may be between about 7-8%. In that example, the radial thickness in each region in cooperation with the respective curvature preferably results in a strain in that region when the ring is substantially straightened of between 4-7%.

The annuloplasty ring is preferably shaped for implant at a native mitral annulus and the core member has an open D-shape with a posterior portion connected by a pair of sides to an anterior portion including the two free ends. Alternatively, the core member is shaped for implant at a native tricuspid annulus. If shaped for mitral annulus implant, the posterior portion has a first radial thickness t₁ and a first radius R of curvature, and the core member has two end regions adjacent the free ends each of which has a second radial thickness t₂ smaller than the first thickness t₁ and a second radius r of curvature smaller than the first radius R of curvature. The core member further may include transition segments between the end regions and the posterior portion which have radial thicknesses t₃ that gradually decrease from the larger first radial thickness t₁ to the smaller second radial thickness t₂. In one embodiment, the core member is saddle-shaped with the two free ends rising upward and the posterior portion also rising upward.

A further understanding of the nature and advantages of the invention will become apparent by reference to the remaining portions of the specification and drawings.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a posterior perspective view of an inner core member of an exemplary annuloplasty ring;

FIG. 2 is a plan view of the inner core member shown in FIG. 1;

FIG. 3 is an anterior perspective view of the inner core member of FIG. 1;

FIG. 4 is an elevational view of the inner core member of FIG. 1 looking at the anterior side thereof;

FIG. 5 is a schematic depiction of a mitral valve and a portion of an adjacent aortic valve with primary anatomical landmarks identified;

FIG. 6 is a plan view of an exemplary annuloplasty ring implanted at a mitral annulus;

FIG. 7 is an elevational view of the exemplary annuloplasty ring after being straightened out for delivery through an access tube;

FIG. 8 shows the annuloplasty ring positioned within an access tube; and

FIG. 9 shows the annuloplasty ring being expelled from the access tube.

DESCRIPTION OF PREFERRED EMBODIMENTS

The present invention provides an annuloplasty ring suitable for implant at a native mitral or tricuspid annulus in need of repair. It should be understood that although a mitral annuloplasty ring is shown and described, a number of features are equally applicable to a tricuspid annuloplasty ring; in particular the desirable curvatures around the ring which limit the maximum strain created in an inner core member when straightened.

A first embodiment of the present application is illustrated in FIGS. 1-4 in which a mitral annuloplasty core member 20 defines a middle or posterior portion 22 and an anterior portion 24 which has free ends 24 a, 24 b separated across a gap G (FIG. 2). Per convention, the mitral annuloplasty core member 20 somewhat resembles an open oval or open D-shape. In a D-shape, the outwardly convex posterior portion 22 forms the curved side and then the free ends 24 a, 24 b together defining a substantially straight anterior portion extending generally between commissures, or possibly the trigones, of the annulus.

A fully assembled annuloplasty ring 28, described in more detail below with reference to FIGS. 6-9, typically includes a soft outer covering 26 closely surrounding the core member 20 for attaching the ring to the annulus with sutures or other means. The core member 20 provides a skeleton for the ring 28, and is merely covered with flexible silicone and/or fabric which conforms to its shape. Therefore, the shape of the ring 28 will be described with reference to the shape of the core member 20.

As seen in FIG. 5, the mitral valve MV seen from above (or looking along the direction of blood flow) includes a posterior leaflet PL that surrounds approximately two thirds of the circumference of the mitral valve and an anterior leaflet AL that occupies approximately one third of the annular circumference, both of which attach at their outer peripheries at the mitral annulus MA. The conventional representation of these two leaflets shows the posterior leaflet below the anterior leaflet, with their line of coaptation, or contact in the flow stream, as a smile-shaped curve. Each leaflet may be divided into three regions: The anterior leaflet AL is divided into three parts: lateral third (A1), middle third (A2) and medial third (A3), while the posterior mitral leaflet PL has a lateral (P1), middle (P2) and medial scallop (P3). Both leaflets are thick at the bases and also at the tips, with central thinning. The mitral valve commissures AC, PC define distinct areas where the anterior and posterior leaflets come together at their insertions with the annulus MA—which can be generalized as the corners of the smile-shaped coaptation line. The anterior portion of the mitral annulus MA attaches to the fibrous trigones and is generally more resistant to tearing and less likely to stretch or elongate than the posterior annulus. The right fibrous trigone RT is a dense junctional area between the mitral, tricuspid, non-coronary sinus NCS of the aortic valve AV and the membranous septum. The left fibrous trigone LT is situated at the junction of both left fibrous borders of the aortic valve and the mitral valve. Although the trigones and commissures are proximate to each other, they are not at the exact same location.

At this point, it is instructive to define coordinate axes for the various directions used to define the ring shape. The term “axis,” “flow axis,” “vertical axis” or “central axis” in reference to the illustrated ring, and other non-circular or non-planar rings, refers to a line generally perpendicular to the ring that passes through the area centroid of the ring when viewed in plan view (e.g., FIG. 2). “Axial” or the direction of the “axis” can also be viewed as being parallel to the direction of blood flow within the valve orifice and thus within the ring when implanted therein. Stated another way, the implanted annuloplasty ring orients about a central flow axis aligned along an average direction of blood flow through the mitral annulus. Although the rings of the present invention are generally 3-dimensional, and saddle-shaped, portions thereof may be planar and lie perpendicular to the flow axis. FIG. 1 shows exemplary coordinate axes with the vertical being the Z-axis, the lateral across a wide dimension of the core member 20 assigned the X-axis, and the longitudinal corresponding to the Y-axis. In general, the core member 20 is arranged “in-plane,” meaning generally arranged in a curve around the flow axis, even though the core contours may be 3D, or other than completely planar. The “in-plane bending moment” is the local stiffness to bending about the flow axis, or in other words bending the core member 20 in its primary plane. The main concern is when bending the core member 20 from its curved shape as in FIG. 2 to be substantially straight, for delivery through an access tube. More specifically, the concern is to ensure the strain of the material does not exceed a threshold level to avoid plastically altering the core member shape.

With reference again to FIGS. 1-4, the core member 20 has an overall saddle shape, with the posterior portion 22 and anterior portion 24 (defined by the free ends 24 a, 24 b) rising upward from left and right sides 40 therebetween. Namely, the posterior portion 22 rises up to a height H, and the anterior portion 24 rises up to a height h. Although there is a gap between the free ends 24 a and 24 b, they generally define upward slopes which extend toward one another, as seen in the plan view of FIG. 2. The upward rise h of the free ends 24 a, 24 b best shown in FIGS. 3 and 4 corresponds to the anterior annulus adjacent to the aortic valve, and avoids having a structure that projects into the left ventricular outflow track where it could impede flow out of the aortic valve. This shape also preserves the natural saddle shape of the anterior leaflet of the mitral valve, reducing the stress on the mitral leaflets during systole. The relative heights of the anterior portion 24 and the posterior portion 22 of the core member 20 are most evident in the anterior view of FIG. 4, in terms of the two heights h and H. Preferably, height H is greater than height h.

With reference to FIGS. 1, 3 and 4, left and right sides 40 of the core member 20 are located at low points axially, while the midpoint of the posterior portion 22 rises to a high point axially on that side, and the two free ends 24 a, 24 b rise up to axial high points on the anterior portion 24. FIG. 1 shows a secondary image below the core member 20 as if it were resting on a reflective reference plane. The sides 40 are shown on the reference plane while the posterior portion 22 and the two free ends 24 a, 24 b separate therefrom in the positive Z-direction. In one embodiment the sides 40 extend in the common reference plane for a short distance. Alternatively, the core member 20 may be entirely curved in the Z-direction with no planar segments.

FIG. 2 illustrates the core member 20 from above in plan view (or in the XY plane) in a relaxed shape and shows a number of dimensional characteristics which enable the core member to be straightened out in the plane of the plan view without exceeding the yield strain for the referred material. First of all, it should be noted that a major axis 50 is drawn across a wide dimension of the core member 20 perpendicular to a minor axis 52. The core member 20 is desirably symmetrical across the minor axis 52, though certain differences may be incorporated to accommodate particular pathological conditions. The desirable dimensional relationships around the core member 20 to result in low strain are nevertheless retained even if the two sides are not identical. A line drawn perpendicular to both the major axis 50 and the minor axis 52, such as through their intersection, extends parallel to the flow, vertical or central axis, as defined above. The bending forces required to straighten the core member 20 are primarily applied about the central axis, or at least about axes parallel thereto.

The core member 20 is desirably made from a superelastic material such as, but not limited to, nitinol (NiTi) or similar superelastic alloys. Superelasticity, sometimes called pseudoelasticity, is an elastic (reversible) response to an applied stress, caused by a phase transformation between the austenitic and martensitic phases of a crystal. More generally, superelasticity permits a material to bend beyond what would conventionally be expected from the particular class of material, such as a metal alloy.

The superelastic core member 20 is designed in such a way that deforming it from the shape shown to a completely linear shape does not exceed the yield strain for nitinol, which is between approximately 7-8%. Namely, the core member 20 as shown in FIG. 2 has a posterior portion 22 with a first radius R of curvature and radial thickness t₁ within an arc labeled θ. Similarly, thin end regions 54 roughly between the sides 40 and the free ends 24 a, 24 b have a smaller second radius r of curvature and a smaller radial thickness t₂ within an arc labeled ß. Transition segments 56 between the posterior portion 22 and the sides 40 have a thickness t₃ that gradually changes between t₁ and t₂. In a preferred embodiment, the radial cross-section of the core member 20 is a solid square with rounded corners, though other shapes may be used. Consequently, the vertical/axial thickness of the posterior portion 22 as seen in FIG. 4 may be equal to the radial thickness t₁, while the vertical/axial thickness of the end regions 54 may be equal to the radial thickness t₂.

One can use the following equations for the relationship between the radius at the neutral axis of a curved beam and the maximum strain it will experience when being straightened:

$\begin{matrix} {e = \frac{l_{1} - l_{0}}{l_{0}}} & {{Eq}.\mspace{14mu} 1} \end{matrix}$

where e is the strain and l₀ and l₁ are the initial and final length of the region which is experiencing strain. In the case of a curved member with an initial radius of curvature R at the neutral axis which subtends an angle of θ in radians and has a thickness of t, the starting and ending lengths, l₀ and l₁, for when the curved member is straightened can be expressed as follows:

$\begin{matrix} {l_{0} = {\left( {R - \frac{t}{2}} \right)\theta}} & {{Eq}.\mspace{14mu} 2} \\ {l_{1} = {R\; \theta}} & {{Eq}.\mspace{14mu} 3} \end{matrix}$

Substituting equations 2 and 3 into equation 1 results in an equation for the maximum strain when a curved beam is straightened:

$\begin{matrix} {e = \frac{\theta \left\lbrack {R - \left( {R - \frac{t}{2}} \right)} \right\rbrack}{\theta \left( {R - \frac{t}{2}} \right)}} & {{Eq}.\mspace{14mu} 4} \end{matrix}$

which simplifies to

$\begin{matrix} {e = \frac{\frac{t}{2}}{R - \frac{t}{2}}} & {{Eq}.\mspace{14mu} 5} \end{matrix}$

Thus, the following equations pertain to the posterior portion 22 and thin regions 54 between the sides 40 and the free ends 24 a, 24 b of the core member 20, respectively:

$\begin{matrix} {e_{1} = \frac{\frac{t_{1}}{2}}{R - \frac{t_{1}}{2}}} & {{Eq}.\mspace{14mu} 6} \\ {e_{2} = \frac{\frac{t_{2}}{2}}{r - \frac{t_{2}}{2}}} & {{Eq}.\mspace{14mu} 7} \end{matrix}$

The strain e₃ within the transition segments 56 between the posterior portion 22 and the sides 40 necessarily changes due to the varying thickness, but is also below the yield strain for nitinol of between approximately 7-8%. In general, the curvature R of the posterior portion 22 is fairly large and therefore the thickness t₁ can also be large, whereas where the curvature r is much tighter as in the end regions 54, the wall thickness t₂ can be thinner. Another way to characterize this design is that the ring has matched radii and radial thicknesses around its periphery which in cooperation result in a strain below the yield strain of the material when the ring is straightened out for MIS delivery.

For an exemplary 24 mm ring, as traditionally measured across the major axis 50 between the inner edges of the core member 20, the radius R of curvature within arc θ (posterior portion 22) is about 0.482 inches (12.24 mm). Assuming the maximum strain to be 7% and solving equation {5} for the thickness t₁ results in the maximum thickness t₁ of 0.063 inches (1.60 mm). Likewise, for the region 54 within arc ß (adjacent the free ends 24 a, 24 b) the radius of curvature is about 0.220 inches (5.59 mm) which results in a maximum calculated thickness of 0.029 inches (0.74 mm).

Still another way to define the beneficial aspects of the exemplary core member 20 is that the in-plane radial thickness at any location depends on the local radius of curvature. As mentioned, looking at FIG. 2, the thickness t₁ in the posterior portion 22 is relatively large because the radius of curvature R is also fairly large. Conversely, in the end regions 54 the thickness t₂ area the section is thinner, but the radius of curvature (r) is much tighter. The strain to straighten a section out goes up with tighter bends and down with thinner sections. With nitinol, the aim is to stay below about 6-7% strain to avoid plasticity.

However, at the same time, the core member 20 must have a minimum bulk for the purpose of providing rigidity to the implanted annuloplasty ring to ensure proper correction or remodeling of the annulus. That is, a purely flexible core member with a small radial thickness, such as a wire, will experience very low strain when straightened, but also will not have the rigidity to remodel the annulus—it will be too floppy. There is thus a trade-off between providing flexibility so as to enable straightening, while also being semi-rigid for remodeling. The more rigid the core member the lower the strain or flexing after implant from the heart beating. Of course, surgeons have varying preferences in this regard, but a semi-rigid ring which can be bent for delivery and then assumes a desired annulus remodeling shape with minimal implanted flexing is considered optimum by most.

So, in practice the local thickness/radius combination preferably results in a strain which is less than but close to the yield strain. For nitinol rings where the material yield strain is between 6-7%, therefore, the strain from straightening out the core member is preferably between 3-6%, more preferably between 4-6%, and most preferably between 5-6%. Similarly, for nitinol rings where the material yield strain is between 7-8%, the strain from straightening out the core member is preferably between 4-7%, more preferably between 5-7%, and most preferably between 6-7%. The following provide examples beyond a 7% strain for a 24 mm ring. For a 5% max strain: t₁=0.046″ (1.17 mm), t₂=0.021″ (0.53 mm). For a 3% max strain: t₁=0.028″ (0.71 mm), t₂=0.013″ (0.33 mm). Again, if the intention is to make the implant as stiff as possible (e.g., lowest strain during heart beating) then it would be desirable to use the highest permissible strain during delivery, which is around 6.5-7% for the nitinol typically used in medical implants.

Further, the same equations and calculations apply to the curvatures in the Z-direction that define the saddle shape to ensure that it could be flexed flat in the Z-direction into a straight configuration for delivery. For instance, the radius of the curvature of the upwardly-bowed posterior portion 22, as best seen in FIG. 4, need only be greater than the radius R in the plan view, assuming the thickness in the vertical dimension is about the same as the thickness t₁ in the radial dimension. The thickness of the ring could certainly be less than the above values depending on what was the desired stiffness of the ring, which could vary from location to location. However, the above examples demonstrate that the ring can be made with a thickness that would be quite rigid yet still able to be fully straightened for delivery through a small incision, catheter, or other tubular structure.

The core member 20 of the MIS annuloplasty ring 28 disclosed herein could be manufactured a number of different ways, including laser cut or stamped from sheet, formed from wire, cut from a tube, etc. Any of these methods could involve post-processing such as machining, grinding, and shape setting to achieve the final desired configuration, both in terms of thickness in the Z-direction as well as the saddle shape.

As will be clear below, the open nature of the core member 20, and ring 28 formed thereby, permits a surgeon to open the structure up into an elongated (straightened) strand for delivery through a small tube such as a catheter or cannula, as will be described below. The annuloplasty ring 28 is advanced into the heart and expelled from the access tube into position at the mitral annulus MA (or tricuspid annulus, as contemplated). The natural elasticity of the superelastic material of the core member 20 enables the ring to transition from the elongated delivery shape to the relaxed ring shape and therefore conform to the target annulus.

FIG. 6 illustrates a final implant position of the annuloplasty ring 28 around the mitral annulus MA. As mentioned above, a soft outer covering 26 closely surrounds the core member 20. The outer covering 26 may be simply surgical-grade fabric, such as polyethylene terephthalate (PET, e.g., DACRON® PET, Invista), or may further include a silicone layer between the core member 20 and outer covering 26. In conventional implantation, an annuloplasty ring is sutured in place using sutures passed through the outer covering 26 and the adjacent annulus. In MIS surgery sutures may also be used, manipulated robotically or otherwise, or alternatives such as clips, staples and the like may be substituted. The present application contemplates the use of all of these methods.

The mitral annuloplasty ring 28 preferably includes two commissure markings 60 that help the surgeon register the ring at the appropriate location around the mitral annulus MA. A third marking 62 may be provided at the midpoint of the posterior portion 22 of the ring. The markings may be lines of colored thread, whereas the outer covering 26 is typically a white fabric. Ink, toner from a laser printing system or even a yarn knit into the cloth can also be used for marker, or the marker may be a radiopaque clip or stitch visible from outside the body under fluoroscopy.

The free ends 24 a, 24 b of the exemplary core member 20 extend beyond the commissure markings 60, into the area of the tough, fibrous trigones RT, LT, as seen in FIG. 6. In a preferred embodiment, each of the free ends 24 a, 24 b extends beyond its respective commissure marking 60 (and thus beyond the native commissures) by a length of between about 5-10 mm.

FIG. 7 is an elevational view of the exemplary annuloplasty ring 28 after being straightened out for delivery through an access tube (not shown). The thicker posterior portion 22, thinner end regions 54 and transition segments 56 are shown along the ring 28. The annuloplasty ring 28 may be straightened via a number of techniques, such as by simply funneling it into one end of a straight rigid tube so that it straightens as it enters, or through a bending implement prior to being inserted into an access tube.

FIG. 8 shows the annuloplasty ring 28 after having been positioned within an access tube 70. The ring 28 is shown with a small residual curvature, though it may be further straightened to fit within an access tube 70 that has an inner diameter just slightly larger than the thickness t₁ of the posterior portion 22 (see FIG. 2). As such, the term “substantially straightened” refers to the elongated shape of the annuloplasty ring 28 as it is shown in FIG. 7, though the ring may be even further straightened. The annuloplasty ring 28 may be advanced through the access tube 70 using a smaller pusher tube 72. In one embodiment, the pusher tube 72 has an inner diameter just slightly larger than the thickness t₂ of the end regions 54, and thus pushes the larger transition segment 56.

FIG. 9 shows the annuloplasty ring 28 being expelled from the access tube 70 by continued advancement of the pusher tube 72. As the ring 28 exits the access tube 70, the leading end region 54 immediately reverts back to its original curvature. In this manner, the surgeon can control the location of the access tube 70 and guide the proper placement of the annuloplasty ring 28 into the final implant position as seen in FIG. 6. Once accurately positioned, anchoring means such as sutures, clips, staples or the like are deployed through the outer covering 26 and into the surrounding annulus.

While the foregoing is a complete description of the preferred embodiments of the invention, various alternatives, modifications, and equivalents may be used. Moreover, it will be obvious that certain other modifications may be practiced within the scope of the appended claims. 

What is claimed is:
 1. An annuloplasty ring, comprising: an inner core member surrounded by an outer covering, the inner core member being formed of a superelastic material and defining a curved relaxed implant shape in plan view which has two free ends spaced across a gap and at least two regions of different curvatures therebetween around a periphery of the core member, the core member having a radial thickness in each region which, in cooperation with a respective curvature in that region, limits a strain within the superelastic material when the ring is substantially straightened to below the yield strain of the superelastic material.
 2. The annuloplasty ring of claim 1, wherein the superelastic material is nitinol.
 3. The annuloplasty ring of claim 2, wherein the yield strain is between about 7-8%.
 4. The annuloplasty ring of claim 1, wherein the yield strain is between about 7-8%.
 5. The annuloplasty ring of claim 4, wherein the radial thickness in each region in cooperation with the respective curvature results in a strain in that region when the ring is substantially straightened of between 4-7%.
 6. The annuloplasty ring of claim 1, wherein the annuloplasty ring is shaped for implant at a native mitral annulus and the core member has an open D-shape with a posterior portion connected by a pair of sides to an anterior portion including the two free ends.
 7. The annuloplasty ring of claim 6, wherein the posterior portion has a first radial thickness t₁ and a first radius R of curvature, and the core member has two end regions adjacent the free ends each of which has a second radial thickness t₂ smaller than the first thickness t₁ and a second radius r of curvature smaller than the first radius R of curvature.
 8. The annuloplasty ring of claim 7, wherein the core member further includes transition segments between the end regions and the posterior portion which have radial thicknesses t₃ that gradually decrease from the larger first radial thickness t₁ to the smaller second radial thickness t₂.
 9. The annuloplasty ring of claim 6, wherein the core member is saddle-shaped with the two free ends rising upward and the posterior portion also rising upward.
 10. The annuloplasty ring of claim 1, wherein the core member is saddle-shaped with the two free ends rising upward and a portion opposite the two free ends also rising upward.
 11. The annuloplasty ring of claim 1, wherein the core member is shaped for implant at a native tricuspid annulus.
 12. An annuloplasty ring, comprising: an inner core member formed of a superelastic material and defining a curved relaxed implant shape in plan view which has two free ends spaced across a gap leading to end regions and a middle portion between the end regions, the core member having a radial thickness in the middle portion larger than a radial thickness in the end regions which, in cooperation with a curvature in the middle portion, limits a strain within the superelastic material when the ring is substantially straightened to below the yield strain of the superelastic material.
 13. The annuloplasty ring of claim 12, wherein the superelastic material is nitinol.
 14. The annuloplasty ring of claim 13, wherein the yield strain is between about 7-8%.
 15. The annuloplasty ring of claim 12, wherein the yield strain is between about 7-8%.
 16. The annuloplasty ring of claim 15, wherein the radial thickness in the middle portion in cooperation with the curvature in the middle portion results in a strain in the middle portion when the ring is substantially straightened of between 4-7%.
 17. The annuloplasty ring of claim 12, wherein the annuloplasty ring is shaped for implant at a native mitral annulus and the core member has an open D-shape with the middle portion connected by a pair of sides to an anterior portion including the two free ends.
 18. The annuloplasty ring of claim 17, wherein the middle portion has a first radial thickness t₁ and a first radius R of curvature, and the core member has two end regions adjacent the free ends each of which has a second radial thickness t₂ smaller than the first thickness t₁ and a second radius r of curvature smaller than the first radius R of curvature.
 19. The annuloplasty ring of claim 18, wherein the core member further includes transition segments between the end regions and the middle portion which have radial thicknesses t₃ that gradually decrease from the larger first radial thickness t₁ to the smaller second radial thickness t₂.
 20. The annuloplasty ring of claim 17, wherein the core member is saddle-shaped with the two free ends rising upward and the middle portion also rising upward.
 21. The annuloplasty ring of claim 12, wherein the core member is saddle-shaped with the two free ends rising upward and the middle portion also rising upward.
 22. The annuloplasty ring of claim 12, wherein the core member is shaped for implant at a native tricuspid annulus. 